Transcutaneous electrical nerve stimulation using novel unbalanced biphasic waveform and novel electrode arrangement

ABSTRACT

The present invention is directed to transcutaneous electrical nerve stimulation (TENS) devices which utilize novel stimulation waveforms and novel arrangements of TENS electrodes to improve the efficiency of power consumption while enhancing therapeutic effects.

REFERENCE TO PENDING PRIOR PATENT APPLICATIONS

This patent application is a continuation of prior U.S. patentapplication Ser. No. 16/175,212, filed Oct. 30, 2018 by Neurometrix,Inc. for TRANSCUTANEOUS ELECTRICAL NERVE STIMULATION USING NOVELUNBALANCED BIPHASIC WAVEFORM AND NOVEL ELECTRODE ARRANGEMENT, which inturn a continuation of prior U.S. patent application Ser. No.15/350,261, filed Nov. 14, 2016 by Neurometrix, Inc. for TRANSCUTANEOUSELECTRICAL NERVE STIMULATION USING NOVEL UNBALANCED BIPHASIC WAVEFORMAND NOVEL ELECTRODE ARRANGEMENT, which in turn is a continuation-in-partof prior U.S. patent application Ser. No. 14/610,757, filed Jan. 30,2015 by NeuroMetrix, Inc. and Shai N. Gozani et al. for APPARATUS ANDMETHOD FOR RELIEVING PAIN USING TRANSCUTANEOUS ELECTRICAL NERVESTIMULATION, which patent application is a continuation of prior U.S.patent application Ser. No. 13/678,221, filed Nov. 15, 2012 byNeuroMetrix, Inc. and Shai N. Gozani et al. for APPARATUS AND METHOD FORRELIEVING PAIN USING TRANSCUTANEOUS ELECTRICAL NERVE STIMULATION, whichin turn claims benefit of (i) prior U.S. Provisional Patent ApplicationSer. No. 61/560,029, filed Nov. 15, 2011 by Shai N. Gozani for SENSUSOPERATING MODEL; and (ii) prior U.S. Provisional Patent Application Ser.No. 61/657,382, filed Jun. 8, 2012 by Shai N. Gozani et al. forAPPARATUS AND METHOD FOR RELIEVING PAIN USING TRANSCUTANEOUS ELECTRICALNERVE STIMULATION.

The six (6) above-identified patent applications are hereby incorporatedherein by reference.

FIELD OF THE INVENTION

This invention relates generally to Transcutaneous Electrical NerveStimulation (TENS) devices that deliver electrical current across theintact skin of a user via electrodes so as to provide symptomatic reliefof chronic pain and other therapeutic benefits. More particularly, thisinvention discloses the construction of novel TENS stimulation waveformsand novel arrangements of TENS electrodes which improve the efficiencyof power consumption while enhancing therapeutic effects.

BACKGROUND OF THE INVENTION

Transcutaneous electrical nerve stimulation (TENS) is the delivery ofelectricity across the intact surface of the skin to activate underlyingnerves; generally with the objective of pain relief. An electricalcircuit generates stimulation pulses with specified characteristics. Oneor more pairs of electrodes, placed on the user's skin, transduce theelectrical pulses and thereby stimulate underlying nerves in order totrigger an analgesic response.

Pain relief from TENS stimulation often begins within 15 minutes of thestimulation onset and may last up to an hour following the completion ofthe stimulation period (also known as a “therapy session”). For optimalpain relief, each therapy session should run for at least 30 minutes andpreferably 60 minutes. To maintain pain relief (i.e., analgesia), TENStherapy sessions typically need to be initiated at regular intervals,such as every other hour. Newly developed wearable TENS devices such asthe QUELL® device by Neurometrix, Inc. of Waltham, Mass., USA provideusers with an option to automatically restart therapy sessions atpre-determined time intervals.

Battery life is an engineering challenge in portable devices. Thewaveform of the stimulation pulse has a significant impact on thebattery life of a TENS device. Symmetric biphasic rectangular pulses areoften used in TENS devices but such pulse waveforms may not be optimalfor maximizing battery life.

The present invention is directed to TENS devices which utilize novelstimulation waveforms and novel arrangements of TENS electrodes toimprove the efficiency of power consumption while enhancing therapeuticeffects.

SUMMARY OF THE INVENTION

The present invention is directed to transcutaneous electrical nervestimulation (TENS) devices which utilize novel stimulation waveforms andnovel arrangements of electrodes to improve the efficiency of powerconsumption while enhancing therapeutic effects.

In one preferred form of the present invention, there is providedapparatus for providing transcutaneous electrical nerve stimulation to auser, said apparatus comprising:

a housing;

a stimulation unit for electrically stimulating nerves using asymmetricbiphasic electrical pulses, wherein during each phase of an asymmetricbiphasic electrical pulse, said stimulation unit generates a voltage atan anode that is higher than a voltage at a cathode so as to allowcurrent to flow from the anode to the cathode, and wherein saidstimulation unit delivers a larger amount of electrical charge in thesecond phase of the asymmetric biphasic electrical pulse than the amountof electrical charge delivered in the first phase of the asymmetricbiphasic electrical pulse using the same anode voltage setting in bothphases of the asymmetric biphasic electrical pulse by taking advantageof the electrical charge accumulated during the first phase of theasymmetric biphasic electrical pulse;

a control unit for controlling the electrical stimulation delivered bysaid stimulation unit; and

an electrode array connectable to said stimulation unit, said electrodearray comprising a substrate and at least first and second electrodes,the at least first and second electrodes being mounted to said substratewith a predetermined arrangement, such that when said substrate isplaced on the user, said first electrode overlays a first nerve but nota second nerve and said second electrode overlays the second nerve butnot the first nerve.

In another preferred form of the present invention, there is providedapparatus for providing transcutaneous electrical nerve stimulation to auser, said apparatus comprising:

a housing;

a stimulation unit for electrically stimulating nerves using asymmetricbiphasic electrical pulses, wherein said stimulation unit delivers alarger amount of electrical charge in the second phase of the asymmetricbiphasic electrical pulse than the amount of electrical charge deliveredin the first phase of the asymmetric biphasic electrical pulse using thesame voltage output level by taking advantage of the electrical chargeaccumulated during the first phase of the asymmetric biphasic electricalpulse;

a control unit for controlling the stimulation delivered by saidstimulation unit; and

an electrode array connectable to said stimulation unit, said electrodearray comprising a substrate and at least first and second electrodes,the at least first and second electrodes being mounted to said substratewith a predetermined arrangement, such that when said substrate isplaced on the user, said first electrode overlays a first nerve but nota second nerve and said second electrode overlays the second nerve butnot the first nerve.

In another preferred form of the present invention, there is provided amethod for providing transcutaneous electrical nerve stimulation therapyto a user, said method comprising:

providing a stimulation unit for generating asymmetric biphasicelectrical pulses, wherein the asymmetric biphasic electrical pulses aregenerated by creating a voltage difference between an anode voltage anda cathode voltage, and the amount of electrical charge delivered in thesecond phase of an asymmetric biphasic electrical pulse is larger thanthe amount of electrical charge delivered in the first phase of theasymmetric biphasic electrical pulse using the same anode voltage duringthe first and second phases of the asymmetric biphasic electrical pulseby taking advantage of the electrical charge accumulated during thefirst phase of the asymmetric biphasic electrical pulse;

providing an electrode array connectable to said stimulation unit, saidelectrode array comprising a substrate and at least first and secondelectrodes, the at least first and second electrodes being mounted tosaid substrate with a predetermined arrangement, such that when saidsubstrate is placed on the user, said first electrode overlays a firstnerve but not a second nerve and said second electrode overlays thesecond nerve but not the first nerve; and

using said stimulation unit and said electrode array to apply asymmetricbiphasic electrical pulses to the skin of a user.

In another preferred form of the present invention, there is provided amethod for providing transcutaneous electrical nerve stimulation to auser, the method comprising:

providing a stimulation unit for generating asymmetric biphasicelectrical pulses, wherein said stimulation unit delivers a largeramount of electrical charge in the second phase of the asymmetricbiphasic electrical pulse than the amount of electrical charge deliveredin the first phase of the asymmetric biphasic electrical pulse withoutincreasing the voltage output of said stimulator unit by takingadvantage of the electrical charge accumulated during the first phase ofthe asymmetric biphasic electrical pulse, and providing an electrodearray connectable to said stimulation unit, said electrode arraycomprising at least first and second electrodes;

placing the electrode array on the user so that the first electrodeoverlays a first nerve but not a second nerve and the second electrodeoverlays the second nerve but not the first nerve; and

using said stimulation unit to apply asymmetric biphasic electricalpulses to the skin of the user.

In another preferred form of the present invention, there is providedapparatus for providing transcutaneous electrical muscle stimulation toa user, said apparatus comprising:

a housing;

a stimulation unit for electrically stimulating muscles using anasymmetric biphasic electrical pulse, wherein during each phase of anasymmetric biphasic electrical pulse, said stimulation unit generates avoltage at an anode that is higher than a voltage at a cathode so as toallow current to flow from the anode to the cathode, and saidstimulation unit delivers a larger amount of electrical charge in thesecond phase of the asymmetric biphasic electrical pulse than the amountof electrical charge delivered in the first phase of the asymmetricbiphasic electrical pulse using the same anode voltage setting in bothphases of the asymmetric biphasic electrical pulse by taking advantageof the electrical charge accumulated during the first phase of theasymmetric biphasic electrical pulse;

a control unit for controlling the stimulation delivered by saidstimulation unit; and

an electrode array connectable to said stimulation unit, said electrodearray comprising a substrate and at least first and second electrodes,the at least first and second electrodes being mounted to said substratewith a predetermined arrangement, such that when said substrate isplaced on the user, said first electrode overlays a first muscle but nota second muscle and said second electrode overlays the second muscle butnot the first muscle.

In another preferred form of the present invention, there is provided amethod for providing transcutaneous electrical muscle stimulationtherapy to a user, said method comprising of the steps of:

placing an electrode array on the skin of a user so that a firstelectrode of said electrode array overlays a first muscle but not asecond muscle and so that a second electrode of said electrode arrayoverlays the second muscle but not the first muscle;

controlling a stimulator unit to generate asymmetric biphasic electricalpulses; and

delivering said asymmetric biphasic electrical pulses to the electrodearray, wherein the second phase of the asymmetric biphasic electricalpulses delivers a larger amount of electrical charge than the firstphase of the asymmetric biphasic electrical pulses without the need toincrease the output voltage of the stimulator unit during the secondphase of the asymmetric biphasic electrical pulses by taking advantageof the electrical charge accumulated during the first phase of theasymmetric biphasic electrical pulse.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other objects and features of the present invention will bemore fully disclosed or rendered obvious by the following detaileddescription of the preferred embodiments of the invention, which is tobe considered together with the accompanying drawings wherein likenumbers refer to like parts, and further wherein:

FIG. 1 is a schematic view of a traditional TENS stimulator usingmonophasic stimulation pulses to stimulate a nerve via a conventionalelectrode arrangement;

FIG. 2 is a schematic view of a traditional TENS stimulator usingbiphasic stimulation pulses to stimulate a nerve via the conventionalelectrode arrangement shown in FIG. 1;

FIG. 3 is a schematic view of a novel TENS stimulator formed inaccordance with the present invention;

FIG. 4 is a schematic view of novel arrangements of TENS electrodesplaced on the lower leg of a user for delivering asymmetric biphasicstimulation pulses regulated by the novel TENS stimulator shown in FIG.3;

FIG. 5 is a schematic view of an asymmetric biphasic stimulation currentpulse and associated voltage profile on the current source of the novelTENS stimulator shown in FIG. 3 when the biphasic stimulation currentpulse is applied to a human body as modeled by a resistor-capacitornetwork;

FIG. 6 is a schematic view of targeted and actual biphasic stimulationcurrent pulse and associated voltage profile of the novel TENSstimulator shown in FIG. 3 when the voltage falls below the target valueto cause actual stimulation current pulse profile to be different fromthe target profile; and

FIG. 7 is a schematic flowchart showing exemplary operation of the novelTENS stimulator shown in FIG. 3 to regulate the high voltage circuitoutput for increasing battery efficiency.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS TENS in General

Transcutaneous electrical nerve stimulation, typically abbreviated asTENS, is the delivery of electricity across the intact surface of theskin so as to activate underlying nerves, generally with the objectiveof pain relief. A conceptual model for how peripheral nerve stimulationleads to pain relief was proposed by Melzack and Wall in 1965 (MelzackR, Wall P D. Pain mechanisms: a new theory. Science. Nov. 19, 1965;150(699):971-979). Their theory suggests that the activation of sensorynerves (Aβ fibers) closes a “pain gate” in the spinal cord whichinhibits the transmission of pain signals carried by nociceptiveafferents (C and Aδ fibers) to the brain. In the past 20 years, theanatomic pathways and molecular mechanisms that may underlie the paingate have been elucidated. Sensory nerve stimulation activates thedescending pain inhibition system, primarily the periaqueductal gray(PAG) and rostroventral medial medulla (RVM) located in the midbrain andmedulla sections of the brainstem, respectively (DeSantana J M, Walsh DM, Vance C, Rakel B A, Sluka K A. Effectiveness of transcutaneouselectrical nerve stimulation for treatment of hyperalgesia and pain.Curr Rheumatol Rep. December 2008; 10(6):492-499). The PAG has neuralprojections to the RVM, which in turn has diffuse bilateral projectionsinto the spinal cord dorsal horn (Ossipov M H, Dussor G O, Porreca F.Central modulation of pain. J Clin Invest. November 2010;120(11):3779-3787). Peripheral nerve stimulation activates the PAG,which triggers the RVM to broadly inhibit pain signal transmission inthe spinal cord dorsal horn. Although it is activated by localizedperipheral nerve stimulation, the descending pain inhibition system hasanalgesic effects that may extend beyond the stimulation site to providebroad pain relief (Dailey D L, Rakel B A, Vance C G, et al.Transcutaneous electrical nerve stimulation reduces pain, fatigue andhyperalgesia while restoring central inhibition in primary fibromyalgia.Pain. November 2013; 154(11):2554-2562).

As described above, TENS induces analgesia by stimulating peripheralnerves. A peripheral nerve is defined as a nerve, which is a collectionof nerve fibers (i.e., axons), that is outside of the brain and spinalcord. Peripheral nerves may comprise nerve fibers that provide sensory,motor or autonomic functions. TENS is primarily intended to stimulatesomatic peripheral nerves, meaning nerve fibers that either bringsensory information into the nervous system or carry motor controlinformation to the muscles. As peripheral nerves descend from the spinalcord they may break off into various branches. Some of these branchesmay be large enough that they are named peripheral nerves. For example,the sciatic nerve, which is formed from spinal nerves in the lumbosacralregion, travels all the way from the lower back to the knee as one majornerve. In the popliteal fossa (i.e., behind the knee) it branches intothe tibial nerve and the common peroneal nerve. These two nerves thenbranch into additional nerves further down the leg and into the foot.Most peripheral nerve branches are smaller and provide limited functionsuch as innervating a muscle or providing sensation to a particular areaof skin. In the latter case, the branch may be described as a cutaneousbranch. In some cases, small branches of peripheral nerves are calledcollaterals.

TENS is characterized by a number of stimulation parameters includingthe stimulation pulse shape, amplitude, duration, pattern, andfrequency. Increasing pulse amplitude or duration, or both, increasesthe pulse intensity (intensity=amplitude*duration) of the TENS therapy.For the same intensity, the relative effectiveness of the stimulationpulse decreases with longer duration due to the strength-durationrelation of a nerve. Stimulation at an intensity below the level ofsensory perception does not provide pain relief, and the degree ofanalgesia is correlated to the stimulation intensity. Scientific studiesand clinical experience suggest that therapeutically effective TENSoccurs at an intensity that feels “strong but comfortable” to the user.

Looking now at FIG. 1, the dose of the TENS therapy is approximatelydefined as C_(E)*f*Δ. Quantity C_(E) 223 is the effective charge perpulse, or the portion of total pulse charge that is actually effectivein stimulating nerve fibers with the resulting nerve pulses travelingproximally to the central nervous system. Quantity f is the pulsefrequency, and its inverse is the pulse period T 224. Quantity Δ 242 isthe therapy session duration. Pulse frequency f is limited by thefrequency response of the nerve, which is determined by the temporalexcitability profile of the nerve including its refractory period, andthe frequency response of the central neural circuits associated withanalgesia. In general, analgesic efficacy drops off over about 100 Hz.Therapy session duration Δ 242 is limited by patient preferences and bythe physiology of the endogenous opioid system, where opioidconcentration starts to drop after about 1 hour of stimulation.

To stimulate a peripheral nerve 205, a TENS stimulator 201 needs atleast two separate contact areas with the skin (e.g., cathode electrode210 and anode electrode 215) so that a closed circuit can be formed.Hydrogel-based electrodes (e.g., cathode electrode 210 and anodeelectrode 215) are preferably used to create the electrical interfacebetween the TENS stimulator and the skin in the contact areas. Importantparameters for electrical pulses are amplitude I_(C) 221 and durationD_(C) 222. For each monophasic pulse 235, its intensity or total pulsecharge IN_(C) is defined as the product of I_(C) and D_(C):IN_(C)=I_(C)*D_(C). The nerve segment under cathode electrode 210 isactivated by an electrical pulse when the intensity IN_(C) exceeds athreshold. The exact threshold value depends upon many factors,including the user's age, height and weight, biophysical characteristicsof the nerve being stimulated, and electrode geometry. In general, thestimulation current amplitude I_(C) 221 must also be above a minimumvalue called the rheobase to activate the nerve segment under theelectrode. For a sequence of monophasic pulses 220, each pulse with thetotal pulse charge IN_(C) contributes effectively to the activation ofthe nerve impulse 216 that travels proximally along the nerve.Therefore, the effective charge C_(E) 223 equals the total pulse charge:C_(E)=IN_(C)=I_(C)*D_(C) in the case of monophasic pulse TENS.

Although monopolar stimulation pulses 220 are efficient in that theeffective charge is equal to the pulse charge, monopolar stimulationpulses are not generally used in TENS stimulation due to known adverseskin reactions under anode 215 and cathode 210 following a prolongedperiod of stimulation. More particularly, during stimulation, negativelycharged ions in the skin will be attracted towards the anode electrodeand their excessive accumulation will cause an acid reaction in the skinarea under the anode 215. Similarly, positively charged ions in the skinwill move to the cathode electrode and their excessive concentrationwill cause an alkaline reaction in the skin area under the cathode 210.To overcome these adverse skin reactions, biphasic stimulation pulsesare typically used in modern TENS devices.

Looking now at FIG. 2, the biphasic pulses 230 typically used in modernTENS devices (e.g., TENS stimulator 201) have a second phase 236following the first phase 235 for each stimulation pulse. The secondphase 236 of the biphasic pulse serves a primary purpose of balancingthe charge delivered during the first phase 235 of the biphasic pulse,thereby preventing adverse skin reactions due to the build-up of chargedions under the electrodes. Electrically, the second phase 236 of thebiphasic pulse reverses the roles of the anode and cathode, but noeffective nerve stimulation should be expected under the “new” cathode(i.e., electrode 215) with the electrode arrangement shown in 245. Thereare two reasons for this. First, the nerve segment under electrode 215is hyperpolarized during the first phase 235 of the biphasic pulse,making it more difficult to be activated by the stimulation currentI_(A) 237 in the second phase 236 of the biphasic pulse. Second, even ifthe nerve segment under electrode 215 could be activated by the secondphase 236 of the biphasic stimulation pulse, any resulting nerve pulses217 could not travel proximally (i.e., towards the central nervoussystem) past electrode 210 because of the refractory period of the nervesegment located under electrode 210. More particularly, the refractoryperiod refers to the inability of a nerve fiber to transmit a secondpulse within a certain time period of the first pulse passing throughthe nerve segment. The refractory period for a human peripheral nerve isgenerally on the order of several milliseconds, while the delay betweenthe two phases of a TENS biphasic pulse is usually less than one-tenthof a millisecond. Hence, the second phase 236 of the biphasic pulse isdelivered to electrode 215 and activates a nerve pulse 217 originatingfrom the nerve segment under electrode 215. Because the nerve segmentunder electrode 210 is still in its refractory period due to nerve pulseactivation earlier from the first phase 235 of the biphasic pulse, thenerve pulse 217 is prevented from traveling through the nerve segmentunder the electrode 210 in the proximal direction. As a result, thesecond phase 236 of the biphasic pulse does not provide the beneficialeffect of activating any nerve pulse that can travel proximally tocontribute to pain relief. In this case, the effective charge is stillC_(E)=I_(C)*D_(C), even though the biphasic pulses have a total pulsecharge of (I_(C)*D_(C)+I_(A)*D_(A)), i.e., the pulse charge I_(C)*D_(C)of the first phase of the biphasic pulse plus the pulse chargeI_(A)*D_(A) of the second phase of the biphasic pulse. In other words,the effective charge C_(E) 233 of the biphasic pulse is essentially justthe pulse charge of the first phase of the biphasic pulse, and thesecond phase of the biphasic pulse does not produce effective nervestimulation. However, as noted above, the use of biphasic pulses isnonetheless beneficial to overcome adverse skin reactions under theelectrodes, and hence has often been adopted with TENS devices.

FIG. 3 provides a functional block diagram for a novel TENS stimulator300 when connected to a patient load 350. Novel TENS stimulator 300 isconfigured to provide biphasic pulses in accordance with the presentinvention, however, for clarity of illustration, FIG. 3 shows only thefirst phase of a biphasic pulse generated by novel TENS stimulator 300(and omits the second phase of the biphasic pulse). Switch 308 can beopen when the TENS stimulator is not delivering current to the patientload. The load to the TENS stimulator output terminals (i.e., anodeterminal 302 and cathode terminal 303) consists of the electrodes, bodytissue, and the interface between the electrodes and skin (note that,even though TENS stimulator 300 is configured to deliver biphasicpulses, terminal 302 is referred to as the “anode” terminal, andterminal 303 is referred to as the “cathode” terminal, since theytypically serve this function during the first phase of the biphasicpulse). A common and effective circuit model of the skin-electrodecontact and tissue volumetric impedance (i.e., the load to thestimulator) is a resistor in series with a parallel resistor-capacitor(RC) circuit as shown inside 350. When switch 308 is closed, anodeterminal voltage V_(A) at the anode terminal 302 is the same as the highvoltage circuit voltage V_(P) at the high voltage circuit output 309. Inorder to deliver an electrical stimulation pulse 320 with a targetcurrent amplitude I 321 for a duration D 322, a minimum voltage biasV_(CS) ^(min) must be maintained at the current source 306. The voltageV_(AC)=V_(A)−V_(C) between anode terminal 302 (i.e., the anode electrodeconnector) and cathode terminal 303 (i.e., the cathode electrodeconnector), as a result of a stimulation current pulse with amplitude I321, is given by

${\tau*\frac{dV_{AC}}{dt}} = {{- V_{AC}} + {I*( {R_{S} + R_{P}} )}}$where the time constant τ=R_(P)*C_(P), i.e., a product of capacitorvalue C_(P) of a capacitive component 351 and resistor value R_(P) of aresistive component 353. Resistor value R_(S) is for a resistivecomponent 352 of the patient load. The above equation has the solutionV _(AC)(t)=I*[R _(S) +R _(P)*(1−e ^(−t/τ))], 0≤t≤D

Using R_(S)=200Ω, R_(P)=130 kΩ, C_(P)=0.1 μF (an equivalent circuitmodel of a healthy subject electrode-skin interface) gives τ=13milliseconds. Stimulation current pulse duration D 322 has a typicalrange of 100-200 microseconds, so we have D<<τ. Given that t<D<<τ,V_(AC)(t) can be approximated byV _(AC)(t)≈I*[R _(S) +t/C _(P)], 0≤t≤D  Eq. (1)To maintain proper operation of the TENS stimulator for delivering acurrent pulse of amplitude I and duration D, the high voltage V_(P) mustbe set high enough to ensure V_(CS) is at least V_(CS) ^(min). Therequired anode voltage V_(A) reaches its maximum value V_(A) ^(max) attime D, and the maximum value is approximately

$V_{A}^{{ma}\; x} = {{{V_{AC}(D)} + {I*R_{I}} + V_{CS}^{m\; i\; n}} = {{I*( {R_{S} + R_{I}} )} + V_{CS}^{m\; i\; n} + {( \frac{I}{C_{P}} )*D}}}$where R_(I) 355 is a sensing resistor with a known value internal to theTENS stimulator for measuring the actual current delivered to thestimulator load 350. In a preferred embodiment of the present invention,the voltage V_(I) across the sensing resistor R_(I) is measured via ananalog-to-digital converter ADC 311 and the microprocessor μPC 312 thencalculates the actual current delivered to the load 350 by dividing thevoltage value V_(I) by the resistance value of R_(I). In a preferredembodiment of the present invention, the value of R_(I) is set to 10Ω.Therefore, the target output voltage V_(P) must be set minimally at thevalue V_(A) ^(max) in order for the TENS stimulator to deliver currentpulses with the required amplitude and duration. In a preferredembodiment, V_(AC)(D) is not directly measured. Rather, the voltageV_(C) is measured by the measurement circuit MMC 314 at time t=D or at aslightly earlier time. High voltage circuit output V_(P) is adjustedthrough microprocessor μPC 312 so that voltage V_(C) is as close aspossible to zero at the end of the stimulation pulse duration D whilemaintaining the current amplitude during the pulse duration D.

The setting of the high voltage V_(P) directly affects battery life.Nominal voltage of a battery V_(B) 305 is about 4.2 volts. Ahigh-voltage generating circuit 310 is used to step-up the batterynominal voltage to the required high voltage V_(P). Power conservationprinciples dictate the following relationship between battery currentdraw I_(B) 301 and high voltage V_(P) at 309:β*I _(B) *V _(B) =I*V _(P) *D/Twhere β (<100%) is the high-voltage circuit efficiency. For a battery ofa given capacity Q_(B), the time T_(B) for the battery capacity todeplete is given by

$T_{B} = \frac{\beta*Q_{B}*T*V_{B}}{I*D*V_{P}}$The actual battery life is shorter than, but proportional to, thistheoretical upper bound. It will, therefore, be appreciated that batterylife can be improved if the high voltage V_(P) can be maintained at theminimum value that is required to deliver a desired stimulation pulse ofamplitude I and duration D.

Maximizing Battery Life Through the Use of Novel Biphasic Waveform withAsymmetric Phase Morphology and Novel Arrangement of TENS Electrodes

The novel TENS stimulator of the present invention is designed tomaximize battery life (i.e., maximize T_(B)) while maintaining the TENStherapeutic effectiveness. More particularly, the novel TENS stimulatorof the present invention utilizes biphasic stimulation pulses (insteadof monophasic pulses). The addition of a second phase with reversedpolarity minimizes skin irritation due to acid or alkaline reactions. Inaccordance with the present invention, a novel asymmetric biphasicstimulation pulse morphology is used which leverages the “voltagemultiplier effect” (see below) to maximize the stimulation intensityeffect of both phases of the pulse without increasing high voltagesettings. Significantly, a novel electrode placement scheme allows bothpositive and negative phases of each biphasic stimulation pulse toeffectively activate peripheral nerves for pain relief.

In this application, the word “asymmetric” is used to describedifferences in the electrical current profiles of the two phases of abiphasic stimulation pulse. In addition, the word “asymmetric” is usedto describe differences in the geometric areas of the two phases of abiphasic stimulation pulse. The area of an electrical stimulation pulsecorresponds to the total charge delivered. Therefore, an asymmetricbiphasic stimulation pulse may deliver unequal charges in each of thetwo phases of the biphasic stimulation pulse, causing the total chargedelivered in the asymmetric biphasic stimulation pulse to be unbalanced(i.e., causing the accumulation of a “net” positive charge or a “net”negative charge under an electrode at the end of the second phase of thebiphasic stimulation pulse).

In a preferred embodiment of the present invention, two electrode padsare placed on the user's body in such a way that each electrode padoverlays a distinct set of nerve fibers. FIG. 4 provides an illustrativeexample. More particularly, an electrode array 405 with two electrodes(e.g., electrode A 402 and electrode B 404) is placed on the lower leg410 of a user, with the two electrodes aligned approximately on the samecross-sectional plane 411. Preferably, electrode array 405 comprises asubstrate having electrode A 402 and electrode B 404 mounted theretowith a predetermined configuration, wherein the substrate is configuredto be held against the skin of the patient in a band-like matter. By wayof example but not limitation, the TENS device may be configured as anadjustable band for mounting circumferentially around the limb of theuser, with electrode array 405 being secured to the skin-facing side ofthe TENS device and captured against the skin of the patient. See, forexample, U.S. Pat. No. 8,948,876, issued Feb. 3, 2015 to NeuroMetrix,Inc. and Shai N. Gozani et al. for APPARATUS AND METHOD FOR RELIEVINGPAIN USING TRANSCUTANEOUS ELECTRICAL NERVE STIMULATION, which patent ishereby incorporated herein by reference. Because peripheral nerves inthe lower leg region primarily traverse in the proximal-to-distaldirection, each electrode 402, 404 will overlay a different nerve (e.g.,electrode A 402 will overlay nerve X 412 and electrode B 404 willoverlay nerve Y 414). In this context, the term “nerve” is used, withoutlimitation, to refer to a collection of nerve fibers such as from amajor peripheral nerve or a branch of a peripheral nerve. By formingelectrode array 405 as a substrate with electrodes 402, 404 mountedthereto with a predetermined configuration, and by appropriately sizingelectrode array 405 for the target anatomy, electrodes 402, 404 may bequickly and easily positioned to overlay the appropriate nerves (e.g.,nerve X 412 and nerve Y 414) when electrode array 405 is secured to theremainder of the TENS device and the TENS device is mounted to the limbof the patient in a band-like manner. The two electrodes 402, 404 areelectrically connected to the cathode and anode terminals 303, 302 ofthe TENS stimulator unit (FIG. 3).

During the stimulation pulse segment HA (i.e., the first phase of thefirst biphasic pulse), nerve X 412 under electrode A 402 is activated byelectrical stimulation with intensity IN_(1A)=I_(C)*D_(C) and theresulting nerve pulses 416 travel proximally to contribute to theeffective dose for pain relief. During the stimulation pulse segment P1B(i.e., the second phase of the first biphasic pulse), nerve Y 414 underelectrode B 404 is activated by electrical stimulation with intensityIN_(1B)=I_(A)*D_(A) and the resulting nerve pulses 418 travel proximallyto contribute to the effective dose for pain relief. Significantly, eventhough the temporal separation between stimulation pulse segment P1A andstimulation pulse segment P1B is typically 0.1 milliseconds or shorter(i.e., less than the refractory period of a peripheral nerve), nerves Xand Y are activated only once (by either stimulation pulse segment P1Aor stimulation pulse segment P1B) due to the non-overlapping nature ofthe nerves, and therefore nerve fibers, under the electrodes and thedisposition of the electrodes relative to the nerves. Therefore, bothnerves X 412 and Y 414 can be activated during the first biphasic pulse(i.e., nerve X can be activated during the first phase of the biphasicpulse and nerve Y can be activated during the second phase of thebiphasic pulse) and contribute to the overall effective dose for painrelief. Because each phase of the biphasic pulse activates a separatenerve with resulting nerve pulses contributing to the effective dose forpain relief, the effective charge C_(E) is the same as the total pulsecharge of (I_(C)*D_(C)+I_(A)*D_(A)) of this biphasic pulse. Statedanother way, by applying the biphasic stimulation pulse across twoelectrodes, wherein each electrode overlies a different nerve, oneelectrode can activate one nerve during the first phase of the biphasicpulse and the other electrode can activate a second nerve during thesecond phase of the biphasic pulse. Therefore, each phase of thebiphasic pulse operates to provide therapeutic nerve stimulation to theuser, and the effective charge C_(E) is provided by both phases of thebiphasic pulse. As a result, with the electrode arrangement shown inFIG. 4, the effective charge C_(E) delivered to the user with a biphasicpulse is (I_(C)*D_(C))+(I_(A)*D_(A)); by contrast, with the electrodearrangement shown in FIG. 2, the effective charge C_(E) delivered to theuser with a biphasic pulse is (I_(C)*D_(C)).

The next biphasic stimulation pulse (i.e., stimulation pulse segment P2Band stimulation pulse segment P2A) occurs at approximately 125milliseconds (80 Hertz) after the first biphasic stimulation pulse,allowing both nerves time to recover from their respective refractoryperiod and to be activated again. During the stimulation pulse segmentP2B, the nerve Y 414 under electrode B 404 is activated by electricalstimulation with intensity IN_(2B)=I_(C)*D_(C). Similarly, the nerve X412 under electrode A 402 is activated during the stimulation pulsesegment P2A with intensity IN_(2A)=I_(A)*D_(A). Again the effectivecharge C_(E) delivered by the biphasic stimulation pulse using theelectrode configuration of FIG. 4 is the same as the total pulse chargeof (I_(C)*D_(C))+(I_(A)*D_(A)) of this biphasic pulse. Therefore, theeffective charge for each biphasic pulse increases to(I_(C)*D_(C))+(I_(A)*D_(A)) with the novel electrode arrangement of FIG.4, which is significantly greater than the effective charge I_(C)*D_(C)using the electrode arrangement 245 of FIG. 2.

Other electrode placements have also been considered. More than oneelectrode can be connected to the anode and cathode connectors of theTENS stimulator unit. Electrodes may also be placed on the body in sucha manner that the nerves underneath the electrodes connected to thecathode terminal are also partially under the electrodes connected tothe anode terminal. Additionally, not all electrodes need to beconnected to either cathode or anode terminals during stimulation.Electrode array 421 in FIG. 4 provides an example. Electrodes A1 422 andB1 424 are first connected to the cathode and anode terminalsrespectively to transmit one or more biphasic pulses. Then electrodes A2423 and B2 425 are connected to the cathode and anode terminals for thenext one or several biphasic pulses. Then electrode A1 422 and B2 425are connected to the cathode and anode terminals again. Then electrodesA2 423 and B1 424 are connected to the cathode and anode terminalsagain. One advantage of alternating the electrode connections may be areduction of nerve habituation as the relative timing of the nervepulses 426 and 427 (traveling along the two nerve fiber bundles X 412and Y 414) becomes variable.

In a preferred embodiment, the target nerve which is to be stimulated isa peripheral sensory nerve. In another preferred embodiment, the targetnerve is a cutaneous branch of a mixed motor and sensory nerve.

FIG. 5 shows an illustrative example of the voltage profile V_(CS)(t)530 across the current source 306 corresponding to the biphasicstimulation pulse 510. Voltage V_(CS)(t) starts out at V_(P) when t<t₁because voltages on all other components to the right of high voltagecircuit 310 are zero as a result of zero current amplitude. At timet=t₁, there is an immediate voltage drop 531 across the resistivecomponents R_(S) 352 and R_(I) 355 (FIG. 3) due to stimulation current.Between the time interval t₁≤t≤t₂, the capacitive component C_(P) 351(FIG. 3) is being charged and the voltage across the load 350 causes afurther gradual drop 532 of the voltage V_(CS)(t). As long as minimumvoltage 541 of V_(CS)(t) stays above V_(CS) ^(min), or V_(CS)(t₂)≥V_(CS)^(min), the current source will function properly during the first phase514 of the biphasic pulse and deliver stimulation at the requiredcurrent amplitude I_(C) 512. At time instance t=t₂, the current source306 is turned off and any voltage across the resistive components R_(S)and R_(I) will become zero, causing a sudden increase 533 of V_(CS)(t).During the time period t₂<t<t₃, the current source 306 remains off andthe capacitive component C_(P) 351 (FIG. 3) in the load 350 dischargesslightly through the resistive component R_(P) 353 (FIG. 3), causing aslight increase 534 of V_(CS)(t). In a preferred embodiment, the delayδ(=t₃−t₂) 515 is set to 100 microseconds. At time instance t=t₃, theload is reversed so that the original voltage drop in the direction frompoint T to point W in the load 350 becomes a voltage increase from pointW to point T since voltage across the capacitor C_(P) 351 (FIG. 3)cannot be changed instantaneously. As a result, the voltage V_(CS)(t)across the current source 306 experiences a sudden increase 535 to alevel usually above V_(P). Between the time interval t₃<t<t₄, thecapacitive component C_(P) is being charged and the voltage across theload 350 causes another gradual drop 536 of the voltage V_(CS)(t).Again, as long as the minimum voltage 542 of V_(CS)(t) stays aboveV_(CS) ^(min), or V_(CS)(t₄)≥V_(CS) ^(min), the current source willfunction properly during the second phase 516 of the biphasic pulse anddeliver stimulation at the required current amplitude I_(A) 518.

If the voltage V_(P) at output terminal 309 of the high voltage circuit310 is set too low, the voltage V_(CS)(t) 530 across the current source306 may not stay above its minimum voltage requirement V_(CS) ^(min)during the first phase of the pulse, or the second phase of the pulse,or both phases of the pulse. When the voltage V_(CS)(t) falls belowV_(CS) ^(min), the current source may not be able to deliver thestimulation current at the required amplitude. FIG. 6 provides anillustrative example of the actual current pulse delivered 550 comparedwith the targeted stimulation current pulse 510. In this case, the firstphase of the stimulation current pulse 552 fails to maintain thetargeted stimulation current amplitude I_(C) during the entire firstphase of the biphasic stimulation pulse while the second phase of thestimulation current pulse 556 matches the targeted stimulation currentamplitude I_(A) throughout the entire second phase of the biphasicstimulation pulse. At time instance t_(C) 553, the voltage V_(CS)(t)falls below the threshold V_(CS) ^(min) because of the voltage increaseacross the capacitor C_(P) (351 in FIG. 3) as a result of the capacitorbeing charged by the stimulation current I_(C). Actual stimulationcurrent amplitude can be monitored via voltage readings from theresistor R₁ as described above. If the actual stimulation currentamplitude is not maintained at the same level throughout the entirephase duration, its stimulation intensity is no longer I_(C)*D_(C). Theactual stimulation intensity is the size of the shaded area 552 and canbe approximated by a summation of a series of stimulation currentamplitude measurements multiplied by the time interval between theconsecutive current measurements. The shaded area 522 sometimes isreferred to as the actual charge delivered by the stimulator during thefirst phase. In one embodiment, if the actual charge delivered is 10%(error percentage) smaller than the target charge I_(C)*D_(C), thevoltage V_(P) is adjusted higher by an amount proportional to the errorpercentage value.

The voltage V_(P) at output terminal 309 of the high voltage circuit 310is regulated so that it stays as low as possible while maintaining theintegrity of the stimulation pulse. In one embodiment, the integrity ofthe stimulation pulse is defined as the amplitude of the stimulationcurrent I(t) of the biphasic stimulation pulse 510 being within apredetermined percentage of the target value I_(C) for all t₁≤t≤t₂ andthe target value I_(A) for all t₃≤t≤t₄. An example of this predeterminedpercentage value is 95%. In another embodiment, the integrity of thestimulation pulse is defined as the intensity IN_(C) ^(A) 552 beingwithin a predetermined percentage of the target intensity value IN_(C)^(T)=I_(C)*D_(C). An example of this predetermined percentage value is90%. The actual amplitude of the stimulation current delivered can bemeasured via the voltage drop V_(I)(t) across the resistor R_(I) 355over time.

FIG. 7 shows a flowchart of a high voltage control algorithm to regulatethe high voltage V_(P). The actual amplitude of the stimulation currentdelivered I(t) can be measured via voltage V_(I) across the resistorR_(I) 355. Step 610 determines the actual stimulation current amplitude.Depending upon the exact definition of the pulse integrity, the mostrecent current amplitude or the integration of current amplitudemeasurements are obtained in step 620. The pulse integrity value iscompared against appropriate threshold values to determine whether thepulse integrity is acceptable in step 630. If the integrity is not OK,the target value of the high voltage circuit output V_(P) is increasedthrough step 640 and the stimulation current amplitude is measured againat a pre-determined time interval. If the integrity is found to be OK instep 630, then the voltage V_(CS)(t)=V_(C)(t)−V_(I)(t) is obtained instep 650. If the voltage exceeded the minimum threshold V_(CS) ^(min),then the target value of the high voltage circuit output V_(P) isdecreased through step 660. In a preferred embodiment, V_(CS) ^(min)=1Volt.

As seen in FIG. 5, the voltage V_(CS)(t) decreases during the firstphase 514 of the biphasic stimulation pulse and during the secondstimulation phase 516 of the biphasic stimulation pulse. The sizes ofthe decreases 532 and 536 are proportional to the stimulation intensityI_(C)*D_(C) and I_(A)*D_(A), respectively. For the first phase 514 ofthe biphasic pulse, the stimulation intensity is limited byV_(P)−I_(C)(R_(S)+R_(I))−V_(CS) ^(min), or the maximum voltage droppossible on the capacitor C_(P) 351 within the load 350. However, thestimulation intensity upper limit for the second phase 516 of thebiphasic pulse is twice as large as that for the first phase 514 of thebiphasic pulse: 2*(V_(P)−I_(C)(R_(S)+R_(I))−V_(CS) ^(min)). This isbecause the voltage on the capacitor C_(P) is added to V_(P) at timeinstance t=t₃ so as to provide the starting voltage at the cathodeterminal 303. Thus, the upper limit of the stimulation intensity for thesecond phase 516 of the biphasic pulse is twice as large as the upperlimit of the stimulation intensity for the first phase 514 of thebiphasic pulse. This phenomenon is sometimes referred to as the “voltagemultiplier effect”. In practice, the value of the voltage multipliereffect is smaller than 2 due to discharge of the capacitor C_(P) duringthe time period t₂≤t≤t₃ and leakage currents in the stimulator circuit.

The amplitude and duration parameters of each phase 514, 516 of thebiphasic pulse can be independently specified. In one embodiment, I_(C)(the stimulation current amplitude of the first phase) and I_(A) (thestimulation current amplitude of the second phase) are set to one commonvalue, and D_(C) (the duration of the first phase) and D_(A) (theduration of the second phase) are set to another common value. Thisconfiguration is the traditional biphasic symmetrical waveform. Inanother embodiment, I_(C) and I_(A) are set to the same value, but D_(A)is set to be longer than D_(C) in order to take advantage of theaforementioned voltage multiplier effect of the stimulator circuit(which is due to the electric charge accumulated in the capacitor C_(P)during the first phase of the biphasic pulse). This configuration is abiphasic asymmetrical waveform.

In yet another embodiment, the amplitude of the second phase I_(A) isset to a value higher than I_(C) so that Q_(C)=I_(C)*D_(C) is the sameas Q_(A)=I_(A)*D_(A) (thus D_(A)<D_(C)). Setting I_(A) higher than I_(C)may not require a higher target value for high voltage circuit outputV_(P) because of the aforementioned voltage multiplier effect. Beingable to set I_(A) higher, without requiring a higher output voltageV_(P), has several advantages. One of these advantages is to allow moreeffective stimulation of the nerve due to the well-knownstrength-duration relationship governing nerve stimulation efficacy. Thecharge required to stimulate a nerve fiber, Q^(TH), increases linearlywith the stimulation duration D as followsQ ^(TH) =b*(D+c)where b and c are constants called the rheobase and chronaxie,respectively. These constants are influenced by many factors thatinclude the biophysical properties of the nerve fiber being stimulated,the characteristics of the intervening tissue between the electrode andnerve fiber, and the characteristics of the stimulation waveform.However, in all cases b>1 and c>0. Therefore, the same nerve fiber willhave a lower Q^(TH) if it is subject to a stimulation pulse with ahigher amplitude I and shorter duration D. In other words, stimulationpulses with the same intensity, but a shorter duration, are moreeffective than those with a longer duration.

In yet another embodiment, both amplitude I_(A) and duration D_(A) ofthe second phase of the biphasic pulse can be set higher than theircorresponding values of the first phase without the need to increase thehigh voltage circuit output V_(P) due to the aforementioned voltagemultiplier effect.

In yet another embodiment, the amplitude of the second phase I_(A) isset to a different value, for example in a random fashion, forconsecutive biphasic pulses such that all amplitude values are within arange. The lower limit of the range can be the amplitude of the firstphase I_(C) and the upper limit of the range can be the highest valuewithout increasing the high voltage circuit output V_(P) requirementthat is needed to support the first phase of the biphasic pulsestimulation. The duration of the second phase of the biphasicstimulation pulse can similarly be set to a range of values. Anadvantage of varying the intensity of the second phase of the biphasicpulse is to reduce nerve habituation and to increase TENS analgesiaeffectiveness.

With the same high voltage circuit output V_(P), the second phase of thebiphasic stimulation pulse is capable of stimulating a nerve whoseQ^(TH) may exceed what the first phase of the biphasic stimulation pulsemay be able to do, even when V_(P)=V_(P) ^(max), where V_(P) ^(max) isthe maximum output voltage that can be delivered by the high voltagecircuit 310. In another embodiment, the high voltage circuit outputV_(P) is adjusted to a level only high enough to guarantee the integrityof the second phase of the biphasic stimulation pulse. At least twoadvantages are obtained with such an approach. Firstly, by leveragingthe voltage multiplier effect at the second phase of the biphasic pulse,some pain relief can be provided to users of the TENS device whoseQ^(TH) cannot be supported with the existing TENS hardware designspecifications if only monophasic pulses are used. Secondly, batterylife can be extended inasmuch as the high voltage circuit output islower than what would otherwise be required.

If the amplitude of the stimulation current remains the same for bothphases of the biphasic stimulation pulse (i.e., I_(C)=I_(A)=I), one canoptimize the duration ratio between the two phases of the biphasic pulseto maximize the total intensity of the biphasic pulse for a given highvoltage V_(P). For simplicity, we assume D_(C)=α*D_(S) andD_(A)=(1−α)*D_(S), where D_(S) is the summation of the first and secondphases of the biphasic pulse. Thus a represents the ratio of theduration of the first phase of the biphasic pulse to the sum of thedurations of the first phase of the biphasic pulse plus the second phaseof the biphasic pulse. Consequently, the total intensity delivered wouldbe I*D_(S). Recall earlier that we have shown that the voltage over thecurrent source 306 is V_(P)−I(R_(S)+R_(I))−V_(E) ^(C), where V_(E) ^(C)is the voltage across the capacitor C_(P) as a result of a current pulsewith amplitude I and duration αD_(S):V_(E) ^(C)=α*I*D_(S). The minimumrequired high voltage output is V_(P) ^(min)=V_(E)^(C)+I(R_(S)+R_(I))+V_(CS) ^(min). Ignoring the voltage change 534 dueto capacitor C_(P) discharge during the inter-phase interval 6 515 (FIG.5), the voltage over the current source 306 at the beginning of secondphase is (at t=V _(P) ^(min) +V _(E) ^(C) −I*(R _(S) +R _(I))=2V _(E) ^(C) +V _(CS)^(min)

The maximum voltage change ΔV_(E) ^(A,max) over the capacitor 351 duringthe second phase of the biphasic pulse must satisfy2V _(E) ^(C) +V _(CS) ^(min) −ΔV _(E) ^(A,max) ≥V _(CS) ^(min) or ΔV_(E) ^(A,max)≤2V _(E) ^(C)Utilizing the aforementioned Eq. (1), we have(1−α)*I*D _(S)≤2*I*D _(S) or α≥⅓.

In a preferred embodiment, the value α is set to 0.36. Using theapproximation of I(R_(S)+R_(I))+V_(CS) ^(min)≈γV_(E) ^(C), where γ<<1.0is a constant, we have the minimum required high voltage for a given aasV _(P) ^(min)=(1+γ)*V _(E) ^(C)=(1+γ)*α*I*D _(S)For a fixed effective charge (total stimulation intensity) I*D_(S), theminimum high voltage setting at α=0.36 is

$\frac{{0.3}6}{0.5} = {72\%}$of what would be required for a symmetric biphasic pulse (i.e., abiphasic pulse having equal duration for both phases, or α=0.5). As aresult, battery life is expected to be 39% longer under the asymmetricpulse duration case (α=0.36) than under the symmetric pulse durationcase (α=0.5) when both cases deliver the same effective charge I*D_(S).

Achieving Net Zero Charge Accumulation by Reversing the Polarity of theBiphasic Pulses

In one form of the present invention, each biphasic pulse has unbalancedtotal charge for its two phases. See, for example, the biphasic waveformshown in FIG. 5. The total charge of the first phase of the biphasicpulse is not balanced by the total charge of the second phase of thebiphasic pulse: I_(C)*D_(C)≠I_(A)*D_(A). Accordingly, in one preferredembodiment of the present invention, the polarity of the leading phaseof consecutive biphasic pulses alternates so as to allow balanced chargeto be delivered to each electrode skin contact area. More particularly,and looking at FIG. 4, the total (negative) charge flowing into the skinarea under electrode A 402 is I_(C)*D_(C) during the first phase HA ofthe biphasic pulse and the total (negative) charge flowing out of thesame skin area is I_(A)*D_(A) during the second phase P1B of thebiphasic pulse. The second biphasic pulse has the polarity of itsleading phase P2B reversed when compared with the polarity of theleading phase P1A of the first biphasic pulse. Consequently, the total(negative) charge flowing out of the skin area is I_(C)*D_(C) during thefirst phase P2B of the biphasic pulse and the total (negative) chargeflowing into the skin area is I_(A)*D_(A) during the second phase P2A ofthe biphasic pulse. So the net charge is effectively balanced over aspan of two biphasic pulses. Similarly, there is no net chargeaccumulation in the skin areas under electrode B 404.

Instead of alternating the polarity of the leading phase for everybiphasic pulse (i.e., as shown in FIG. 4), the frequency of alternatingthe polarity of the leading phase of the biphasic pulses can be set to alower value as long as the zero net charge accumulation is maintainedacross a reasonable period of time. In other words, the polarity of theleading phase of the biphasic pulses may be changed every two pulses, orevery three pulses, or every four pulses, etc., so long as there is nonet charge accumulation over a selected period of time (which is not solong as to result in adverse skin reactions under the electrodes). Inone preferred embodiment, polarity alternating occurs every two biphasicpulses.

Experimental Data Demonstrating Benefits of Asymmetric Biphasic PulseStimulation

To demonstrate the benefits of the asymmetric pulse duration approachdisclosed herein, ten healthy subjects were recruited and consented toparticipate in a study to compare the effectiveness of two differentbiphasic pulse stimulation patterns. Pattern A was the symmetricbiphasic pulse pattern wherein both phases of the biphasic pulse had thesame amplitude and duration, e.g., such as the biphasic pulse patternshown in FIG. 2. The duration was fixed at 100 microseconds andamplitude was allowed to be adjusted by each subject to evoke the firstsensation of electrical stimulation. Pattern B was the asymmetricbiphasic pulse pattern wherein the second phase of the biphasic pulsehad a longer duration (180 microseconds) than the first phase of thebiphasic pulse (100 microseconds), e.g., such as the biphasic pulsepattern shown in FIG. 5. The amplitude of both phases of the Pattern Basymmetric biphasic pulse pattern was kept the same and allowed to beadjusted by each subject so as to evoke the same first sensation ofelectrical stimulation as for Pattern A. Subjects were blinded to thestimulation pattern used and carried out the sensation thresholddiscovery process three times for each stimulation pattern. During eachtrial, the subject indicated the minimum stimulation pulse amplitudethat evoked the first sensation of electrical stimulation. Table 1summarizes the study results. For each subject, the three identifiedstimulation pulse amplitudes (in milliamps) were averaged for Pattern Aand Pattern B, respectively. Among the ten test subjects, the minimumstimulation current amplitude to evoke a first sensation of electricalstimulation was 14%-35% lower for asymmetric pulse pattern B than thatfor symmetric pulse pattern A. Since both pulse patterns had the sameduration in the first phase of the biphasic pulse, the reduction instimulation current amplitude required to evoke the first sensation canonly be attributed to longer duration of the second phase of theasymmetric pulse Pattern B. Earlier analyses indicate that the minimumhigh voltage V_(P) required will be lower if the first phase currentamplitude is lower. Because of the voltage multiplier effect, the highvoltage requirement for any pulse with a second phase duration less than2-times the first phase duration will be approximately the same as thatfor the first phase.

TABLE 1 SubjID Pattern B Pattern A Difference (mA) Difference (%) 1 10.014.8 −4.8 −32.2% 2 12.1 16.9 −4.7 −28.2% 3 13.9 21.3 −7.3 −34.5% 4 9.113.6 −4.5 −32.9% 5 17.5 22.3 −4.8 −21.6% 6 12.5 14.5 −2.1 −14.4% 7 9.814.3 −4.4 −31.0% 8 11.8 15.9 −4.1 −25.8% 9 14.0 16.6 −2.6 −15.7% 10 7.110.3 −3.2 −30.7% Mean −26.7% Comparison of minimum current amplituderequired to evoke first stimulation sensation in human subjects. PatternA refers to biphasic pulse with same pulse duration for both phases (100μs). Pattern B refers to biphasic pulse with the pulse duration forsecond phase (180 μs) longer than the first pulse duration (100 μs).Amplitude for both phases are the same in either pulse patterns. Resultsare the average of three trials.

Direct Muscle Stimulation Using Asymmetric Biphasic Electrical Pulseswith an Alternating Polarity of the Leading Phase of the Pulses

Electrical pulses can also be used to stimulate muscles directly so asto cause muscle contractions. Electrical pulses are delivered throughelectrodes on the skin. Instead of placing the electrodes so as tooverlay peripheral nerves, the electrodes are placed on the skin indirect proximity to the muscles which are to be stimulated. Electricalmuscle stimulation (EMS) can be used to improve muscle strength inathletes, to prevent muscle atrophy in patients with musculoskeletalinjuries, and to provide external muscle control when the nerve supplyto the muscle is compromised.

Portable EMS devices face similar challenges to TENS devices in terms ofbattery life and stimulation intensity. Applying asymmetric biphasicstimulation pulses in EMS can overcome these challenges by leveragingcharge build-up during the first phase of the biphasic stimulation pulsein order to deliver more powerful stimulation during the second phase ofthe biphasic stimulation pulse. Delivering stronger stimulation pulseswith a higher amplitude or a longer duration in the second phase of thebiphasic stimulation pulse, without requiring an increase in the outputof the high-voltage circuit, will lead to savings in battery life.Alternating the polarity of the leading phase of the biphasic electricalpulses allows the muscles under each electrode to receive the same totalstimulation intensity. Alternating the polarity of the leading phases ofthe biphasic electrical pulses also ensures zero net charge flowing intoeach electrode even when asymmetric biphasic pulses are used.

Modifications of the Preferred Embodiments

It should be understood that many additional changes in the details,materials, steps and arrangements of parts, which have been hereindescribed and illustrated in order to explain the nature of the presentinvention, may be made by those skilled in the art while still remainingwithin the principles and scope of the invention.

What is claimed is:
 1. Apparatus for providing transcutaneous electricalmuscle stimulation to a user, said apparatus comprising: a stimulationunit for electrically stimulating one or more muscles using anasymmetric biphasic electrical pulse from a current source, whereinduring the first phase and the second phase of an asymmetric biphasicelectrical pulse, said stimulation unit uses a same voltage level at ananode, wherein said stimulation unit delivers a larger amount ofelectrical charge in the second phase of the asymmetric biphasicelectrical pulse than the amount of electrical charge delivered in thefirst phase of the asymmetric biphasic electrical pulse, and wherein thesame anode voltage level is selected to maintain a minimum voltagerequired for the current source during the first phase of the asymmetricbiphasic electrical pulse; a control unit for controlling thestimulation delivered by said stimulation unit; and an electrode arrayconnectable to said stimulation unit, said electrode array comprising asubstrate and at least first and second electrodes.
 2. Apparatusaccording to claim 1 wherein the at least first and second electrodesare mounted to said substrate with a predetermined arrangement, so thatwhen said substrate is placed on one location of the user's body, saidfirst electrode overlays a first muscle underneath the electrode arraybut not a second muscle underneath the electrode array and said secondelectrode overlays the second muscle underneath the electrode array butnot the first muscle underneath the electrode array.
 3. Apparatusaccording to claim 2 wherein the said first electrode and said secondelectrode both overlay a third muscle underneath the electrode array. 4.Apparatus according to claim 1 wherein said control unit is configuredto cause said stimulation unit to deliver discrete asymmetric biphasicelectrical pulses.
 5. Apparatus according to claim 4 wherein thepolarity of the first phase of the discrete asymmetric biphasicelectrical pulses varies.
 6. Apparatus according to claim 4 wherein thepolarity of the first phase of each discrete asymmetric biphasicelectrical pulse varies so as to ensure that an equal amount of positiveand negative charges flow into each electrode within a predeterminedtime period.
 7. Apparatus according to claim 4 wherein the discreteasymmetric biphasic electrical pulses are delivered at a constantfrequency.
 8. Apparatus according to claim 4 wherein the discreteasymmetric biphasic electrical pulses are delivered at a randomfrequency.
 9. Apparatus according to claim 1 wherein said control unitcontrols the anode voltage of said stimulation unit.
 10. Apparatusaccording to claim 9 wherein said control unit controls said anodevoltage based on at least one of the following: (i) the cathode voltage,and (ii) measurements of the asymmetric biphasic electrical pulses. 11.Apparatus according to claim 1 wherein said control unit controls theamplitude and duration of the first and second phases of the asymmetricbiphasic electrical pulses.
 12. Apparatus according to claim 11 whereinthe amplitude of the second phase of said asymmetric biphasic electricalpulses is the same as that of the first phase of said asymmetricbiphasic electrical pulses.
 13. Apparatus according to claim 11 whereinthe amplitude of the second phase of said asymmetric biphasic electricalpulses is greater than that of the first phase of said asymmetricbiphasic electrical pulses.
 14. Apparatus according to claim 11 whereinthe duration of the second phase of said asymmetric biphasic electricalpulses is the same as that of the first phase of said asymmetricbiphasic electrical pulses.
 15. Apparatus according to claim 11 whereinthe duration of the second phase of said asymmetric biphasic electricalpulses is greater than that of the first phase of said asymmetricbiphasic electrical pulses.
 16. Apparatus for providing transcutaneouselectrical muscle stimulation to a user, said apparatus comprising: astimulation unit for electrically stimulating one or more muscles usingan asymmetric biphasic electrical pulse from a current source, whereinduring the second phase of the asymmetric biphasic electrical pulse,said stimulation unit uses an anode voltage level that is no greaterthan the anode voltage level used during the first phase of theasymmetric biphasic electrical pulse, and wherein said stimulation unitdelivers a larger amount of electrical charge in the second phase of theasymmetric biphasic electrical pulse than the amount of electricalcharge delivered in the first phase of the asymmetric biphasicelectrical pulse; a control unit for controlling the stimulationdelivered by said stimulation unit; and an electrode array connectableto said stimulation unit, said electrode array comprising a substrateand at least first and second electrodes.
 17. A method for providingtranscutaneous electrical muscle stimulation therapy to a user, saidmethod comprising: providing a stimulation unit for generatingasymmetric biphasic electrical pulses, wherein the stimulation unitdelivers a larger amount of electrical charge in the second phase of anasymmetric biphasic electrical pulse than the amount of electricalcharge delivered in the first phase of the asymmetric biphasicelectrical pulse, and wherein a same anode voltage level is used by thestimulation unit during the first and second phases of the asymmetricbiphasic electrical pulse; providing an electrode array connectable tosaid stimulation unit, said electrode array comprising a substrate andat least first and second electrodes; and using said stimulation unitand said electrode array to apply asymmetric biphasic electrical pulsesto the skin of a user.
 18. A method according to claim 17 wherein the atleast first and second electrodes are mounted to said substrate with apredetermined arrangement, so that when said substrate is placed on onelocation of the user's body, said first electrode overlays a firstmuscle underneath the electrode array but not a second muscle underneaththe electrode array and said second electrode overlays the second muscleunderneath the electrode array but not the first muscle underneath theelectrode array.
 19. A method according to claim 18 wherein the firstelectrode activates the first muscle during the first phase of theasymmetric biphasic electrical pulse and the second electrode activatesthe second muscle during the second phase of the asymmetric biphasicelectrical pulse.
 20. A method according to claim 17 wherein saidstimulation unit delivers a sequence of discrete asymmetric biphasicelectrical pulses.
 21. A method according to claim 20 wherein saidasymmetric biphasic electrical pulses are delivered at a randomfrequency, wherein said random frequency is within a predeterminedrange.
 22. A method according to claim 20 wherein said asymmetricbiphasic electrical pulses vary the polarity of the first phase of theasymmetric biphasic electrical pulses.
 23. A method according to claim22 wherein the pattern of variations of the first phases of theasymmetric biphasic electrical pulses ensures that an equal amount ofpositive and negative charges flow into each electrode within apredetermined time period.
 24. A method according to claim 17 whereinsaid stimulation unit controls the amplitude of the two phases of theasymmetric biphasic electrical pulses independently.
 25. A methodaccording to claim 17 wherein said stimulation unit controls theduration of the two phases of the asymmetric biphasic electrical pulsesindependently.
 26. A method according to claim 17 wherein saidstimulation unit controls the anode voltage based on at least one of thefollowing: (i) the cathode voltage, and (ii) measurements of theasymmetric biphasic electrical pulses.
 27. A method for providingtranscutaneous electrical muscle stimulation therapy to a user, saidmethod comprising: providing a stimulation unit for generatingasymmetric biphasic electrical pulses, wherein the stimulation unitdelivers a larger amount of electrical charge in the second phase of anasymmetric biphasic electrical pulse than the amount of electricalcharge delivered in the first phase of the asymmetric biphasicelectrical pulse, and wherein the stimulation unit uses an anode voltagelevel in the second phase that is no greater than the anode voltagelevel used in the first phase; providing an electrode array connectableto said stimulation unit, said electrode array comprising a substrateand at least first and second electrodes; and using said stimulationunit and said electrode array to apply asymmetric biphasic electricalpulses to the skin of a user.